Method for bone structure prognosis and simulated bone remodeling

ABSTRACT

Described herein are methods for analyzing bone structure and/or bone density, methods for estimating fracture risk in a subject as well as methods for monitoring the efficacy of an agent on bone structure and/or bone density.

CROSS-REFERENCE TO RELATED APPLICATIONS

This application is a continuation of U.S. application Ser. No. 11/846,018 filed Aug. 28, 2007, which claims the benefit of U.S. provisional application Ser. No. 60/823,736, filed Aug.28, 2006. U.S. application Ser. No. 11/846,018 is also a continuation-in-part of U.S. application Ser. No. 10/944,478, filed Sep. 17, 2004, now U.S. Pat. No. 8,073,521, which in turn claims the benefit of U.S. provisional application Ser. No. 60/503,916, filed Sep. 19, 2003. Each of the above-described documents is incorporated by reference herein in its entirety.

TECHNICAL FIELD

The present invention is in the field of imaging and analysis thereof. In particular, methods for accurately analyzing images to determine bone mineral density and/or bone structure are described along with methods for bone modeling and remodeling.

BACKGROUND

Imaging techniques are important diagnostic tools, particularly for bone related conditions. Currently available techniques for the noninvasive assessment of the skeleton for the diagnosis of osteoporosis or the evaluation of an increased risk of fracture include dual x-ray absorptiometry (DXA) (Eastell et al. (1998) New Engl J. Med 338:736-746); quantitative computed tomography (QCT) (Cann (1988) Radiology 166:509-522); peripheral DXA (pDXA) (Patel et al. (1999) J Clin Densitom 2:397-401); peripheral QCT (pQCT) (Gluer et. al. (1997) Semin Nucl Med 27:229-247); x-ray image absorptiometry (RA) (Gluer et. al. (1997) Semin Nucl Med 27:229-247); and quantitative ultrasound (QUS) (Njeh et al. “Quantitative Ultrasound: Assessment of Osteoporosis and Bone Status” 1999, Martin-Dunitz, London England; U.S. Pat. No. 6,077,224, incorporated herein by reference in its entirety). (See, also, WO 99/45845; WO 99/08597; and U.S. Pat. No. 6,246,745).

DXA of the spine and hip has established itself as the most widely used method of measuring BMD. Tothill, P. and D. W. Pye, (1992) Br J Radiol 65:807-813. The fundamental principle behind DXA is the measurement of the transmission through the body of x-rays of 2 different photon energy levels. Because of the dependence of the attenuation coefficient on the atomic number and photon energy, measurement of the transmission factors at 2 energy levels enables the area densities (i.e., the mass per unit projected area) of 2 different types of tissue to be inferred. In DXA scans, these are taken to be bone mineral (hydroxyapatite) and soft tissue, respectively. However, it is widely recognized that the accuracy of DXA scans is limited by the variable composition of soft tissue. Because of its higher hydrogen content, the attenuation coefficient of fat is different from that of lean tissue. Differences in the soft tissue composition in the path of the x-ray beam through bone compared with the adjacent soft tissue reference area cause errors in the BMD measurements, according to the results of several studies. Tothill, P. and D. W. Pye, (1992) Br J Radiol, 65:807-813; Svendsen, O. L., et al., (1995) J Bone Min Res 10:868-873. Moreover, DXA systems are large and expensive, ranging in price between $75,000 and $150,000.

Quantitative computed tomography (QCT) is usually applied to measure the trabecular bone in the vertebral bodies. Cann (1988) Radiology 166:509-522. QCT studies are generally performed using a single kV setting (single-energy QCT), when the principal source of error is the variable composition of the bone marrow. However, a dual-kV scan (dual-energy QCT) is also possible. This reduces the accuracy errors but at the price of poorer precision and higher radiation dose. Like DXA, however, QCT are very expensive and the use of such equipment is currently limited to few research centers.

Quantitative ultrasound (QUS) is a technique for measuring the peripheral skeleton. Njeh et al. (1997) Osteoporosis Int 7:7-22; Njeh et al. Quantitative Ultrasound: Assessment of Osteoporosis and Bone Status. 1999, London, England: Martin Dunitz. There is a wide variety of equipment available, with most devices using the heel as the measurement site. A sonographic pulse passing through bone is strongly attenuated as the signal is scattered and absorbed by trabeculae. Attenuation increases linearly with frequency, and the slope of the relationship is referred to as broadband ultrasonic attenuation (BUA; units: dB/MHz). BUA is reduced in patients with osteoporosis because there are fewer trabeculae in the calcaneus to attenuate the signal. In addition to BUA, most QUS systems also measure the speed of sound (SOS) in the heel by dividing the distance between the sonographic transducers by the propagation time (units: m/s). SOS values are reduced in patients with osteoporosis because with the loss of mineralized bone, the elastic modulus of the bone is decreased. There remain, however, several limitations to QUS measurements. The success of QUS in predicting fracture risk in younger patients remains uncertain. Another difficulty with QUS measurements is that they are not readily encompassed within the WHO definitions of osteoporosis and osteopenia. Moreover, no intervention thresholds have been developed. Thus, measurements cannot be used for therapeutic decision-making.

There are also several technical limitations to QUS. Many devices use a foot support that positions the patient's heel between fixed transducers. Thus, the measurement site is not readily adapted to different sizes and shapes of the calcaneus, and the exact anatomic site of the measurement varies from patient to patient. It is generally agreed that the relatively poor precision of QUS measurements makes most devices unsuitable for monitoring patients' response to treatment. Gluer (1997) J Bone Min Res 12:1280-1288.

Radiographic absorptiometry (RA) is a technique that was developed many years ago for assessing bone density in the hand, but the technique has recently attracted renewed interest. Gluer et al. (1997) Semin Nucl Med 27:229-247. With this technique, BMD is measured in the phalanges. The principal disadvantage of RA of the hand is the relative lack of high turnover trabecular bone. For this reason, RA of the hand has limited sensitivity in detecting osteoporosis and is not very useful for monitoring therapy-induced changes.

Peripheral x-ray absorptiometry methods such as those described above are substantially cheaper than DXA and QCT with system prices ranging between $15,000 and $35,000. However, epidemiologic studies have shown that the discriminatory ability of peripheral BMD measurements to predict spine and hip fractures is lower than when spine and hip BMD measurements are used. Cummings et al. (1993) Lancet 341:72-75; Marshall et al. (1996) Br Med J 312:1254-1259. The main reason for this is the lack of trabecular bone at the measurement sites used with these techniques. In addition, changes in forearm or hand BMD in response to hormone replacement therapy, bisphosphonates, and selective estrogen receptor modulators are relatively small, making such measurements less suitable than measurements of principally trabecular bone for monitoring response to treatment. Faulkner (1998) J Clin Densitom 1:279-285; Hoskings et al. (1998) N Engl J Med 338:485-492. Although attempts to obtain information on bone mineral density from dental x-rays have been attempted (See, e.g., Shrout et al. (2000) J. Periodonol. 71:335-340; Verhoeven et al. (1998) Clin Oral Implants Res 9(5):333-342), these have not provided accurate and reliable results.

Furthermore, current methods and devices do not generally take into account bone structure analyses. See, e.g., Ruttimann et al. (1992) Oral Surg Oral Med Oral Pathol 74:98-110; Southard & Southard (1992) Oral Surg Oral Med Oral Pathol 73:751-9; White & Rudolph, (1999) Oral Surg Oral Med Oral Pathol Oral Radiol Endod 88:628-35.

Thus, although a number of devices and methods exist for evaluating bone, there are a number of limitations on such devices and methods. Consequently, the inventors have recognized the need, among other things, to provide methods and compositions that result in the ability to obtain accurate bone mineral density and bone structure information from images (e.g., radiographic images) containing the bone and related subject data.

SUMMARY

In one aspect, the invention includes a method for analyzing bone structure or bone density, the method comprising the steps of: obtaining an image of a subject, wherein the image comprises an image of the subject's bone; estimating probable volumetric structure of bone; and measuring one or more parameters of estimated volumetric structure of bone. The image may be an MRI or an x-ray image. In certain embodiments, the parameter measured comprises structural strength.

In another aspect, the invention comprises a method for estimating fracture risk in a subject, the method comprising the steps of: obtaining an image of the subject, wherein the image comprises an image of the subject's bone; estimating probable volumetric structure of bone; measuring one or more parameters of estimated volumetric structure of bone; and comparing the measurements to measurements of population data, thereby estimating fracture risk in the subject.

In yet another aspect, the invention comprises a method for estimating future fracture risk in a subject, the method comprising the steps of: obtaining an image of the subject, wherein the image comprises an image of the subject's bone; estimating probable volumetric structure of bone; measuring bone quality parameters of estimated volumetric structure of bone; simulating bone remodeling using the estimated volumetric structure of bone; and comparing the bone quality measurements on resultant structures from simulation of bone remodeling to measurements of population data, thereby predicting future fracture risk in the subject under simulation conditions. In certain embodiment, the simulation of bone remodeling is of therapeutic interventions. In other embodiments, the simulation of bone remodeling is of disease progression.

In another aspect, the invention includes a method for monitoring the effect of an agent on bone quality and/or a system for drug discovery. The method generally comprises: (a) obtaining bone quality (e.g., bone density or bone structure) measurements on a subject, wherein the measurements are obtained using any of the methods described herein; (b) administering an agent to the subject; (c) obtaining bone quality (e.g., bone density or bone structure) measurements of the subject after administration of the agent, wherein the measurements are obtained using any of the methods described herein; and (d) comparing bone quality (e.g., bone density or bone structure) measurements from steps (a) and (c).

In various embodiments of the invention, one or more measurements pertaining to, without limitation, bone mineral density, bone architecture or structure, macro-anatomy, and/or bone biomechanics, may be generated from two or more x-ray beam rotation angles. The x-rays may be acquired, without limitation, by a conventional radiography unit, a conventional tomography unit (e.g., CT scan), or a digital radiography unit (e.g., digital radiography (DR) or computed radiography (CR) systems). If a DR or CR system is implemented, images may be obtained from multiple rotation angles so as to allow tomographic reconstruction.

In one aspect, the invention includes a method for analyzing bone. The method generally includes obtaining an image(s) of a subject by digital radiography (DR) and computed radiography (CR) over multiple x-ray beam rotation angles, wherein the image comprises an image of the subject's bone. One or more parameters are determined based, at least in part, on the image(s). The one or more parameters include at least one of a macroanatomical parameter, a biomechanical parameter, bone structure, structural strength, and bone mineral density.

In related embodiments, the one or more parameters determined may be compared to measurements of population data, thereby estimating fracture risk in the subject. These and other embodiments of the present invention will readily occur to those of ordinary skill in the art in view of the disclosure herein.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1, panels A-I, are reproductions of various projections of volume images (uCT, MRI) when simulated remodeling techniques are applied. FIG. 1A depicts no erosion (Level 0) and FIGS. 1A to I depict further erosions of each the previous panels (Levels 1 to 8).

FIG. 2 is a graph depicting 2D bone area ratio measurements from various simulated bone remodeling levels versus corresponding 3 D volume ratio measurements.

FIG. 3 is a schematic diagram depicting an exemplary configuration of rods and plates generated with a model to simulate a stage of bone growth.

FIG. 4, panels A-D, depict projections and structure extraction of simulated bone growth in vertebra with various configurations of rod and plate trabecular bone.

FIG. 5, panels A and B, are graphs depicting relationships of measurements from projection vs. model density. FIG. 5A depicts area ratio vs 3D structure density. FIG. 5B depicts structure separation versus 3D structure density.

FIG. 6, panels A to D, depicts exemplary projections of rods and plates. FIGS. 6A and 6B are projections at model density 410. FIGS. 6C and 6D are projections at model density 450.

FIG. 7, panels A and B, are graphs depicting projection vs. 3D structure density. FIG. 7A depicts segment number/area vs. 3D structure density. FIG. 7B depicts structure perimeter vs. 3D structure density.

FIG. 8, panels A and B, are graphs depicting simulated erosion. FIG. 8A depicts 3D bone volume/total volume vs. erosion level. FIG. 8B depicts 2D area ratio vs. erosion level.

FIG. 9 is a graph depicting 2D bone area ratio vs. 3D volume ratio.

FIG. 10, panels A to D, are graphs depicting various 2D parameters in simulated erosions. FIG. 10A depicts node count versus erosion level. FIG. 10B depicts trabecular bone pattern factor vs. erosion level. FIG. 10C depicts skeleton network length vs. erosion level. FIG. 10D depicts interconnectivity index vs. erosion level.

FIG. 11 is a schematic flowchart depicting various steps involved in an exemplary method of bone structure prognosis and simulated bone remodeling.

DESCRIPTION

The following description is presented to enable any person skilled in the art to make and use the invention. Various modifications to the embodiments described will be readily apparent to those skilled in the art, and the generic principles defined herein can be applied to other embodiments and applications without departing from the spirit and scope of the present invention as defined by the appended claims. Thus, the present invention is not intended to be limited to the embodiments shown, but is to be accorded the widest scope consistent with the principles and features disclosed herein. To the extent necessary to achieve a complete understanding of the invention disclosed, the specification and drawings of all issued patents, patent publications, and patent applications cited in this application are incorporated herein by reference.

The practice of the present invention employs, unless otherwise indicated, currently conventional methods of imaging and image processing within the skill of the art. Such techniques are explained fully in the literature. See, e.g., WO 02/22014, X-Ray Structure Determination: A Practical Guide, 2^(nd) Edition, editors Stout and Jensen, 1989, John Wiley & Sons, publisher; Body CT: A Practical Approach, editor Slone, 1999, McGraw-Hill publisher; The Essential Physics of Medical Imaging, editors Bushberg, Seibert, Leidholdt Jr & Boone, 2002, Lippincott, Williams & Wilkins; X-ray Diagnosis: A Physician's Approach, editor Lam, 1998 Springer-Verlag, publisher; Dental Radiology: Understanding the X-Ray Image, editor Laetitia Brocklebank 1997, Oxford University Press publisher; and Digital Image Processing, editor Kenneth R. Castleman, 1996 Prentice Hall, publisher; The Image Processing Handbook, editor John C. Russ, 3^(rd) Edition, 1998, CRC Press; Active Contours: The Application of Techniques from Graphics, Vision, Control Theory and Statistics to Visual Tracking of Shapes in Motion, Editors Andrew Blake, Michael Isard, 1999 Springer Verlag. As will be appreciated by those of skill in the art, as the field of imaging continues to advance methods of imaging currently employed can evolve over time. Thus, any imaging method or technique that is currently employed is appropriate for application of the teachings of this invention as well as techniques that can be developed in the future. A further detailed description of imaging methods is not provided in order to avoid obscuring the invention.

Described herein are methods for bone structure prognosis and simulated bone remodeling. Bone remodeling is a physiological process in which continuous bone resorption (loss) and bone formation (gain) occurs. When the bone resorption rate is higher than bone formation rate, a net bone loss occurs, thereby causing an overall reduction of bone mass and quality. Conversely, when bone formation rate is higher than the resorption rate, a net bone gain occurs. Using the techniques described herein, bone loss or bone gain can be simulated in any given subject. In addition, the efficacy of drug therapy can be validated, putative drugs or therapies can be evaluated, and better models can be obtained for bone loss. The methods described herein also allow for the generation of non-linear mathematical relationships for the bone loss and gain models as well as improved methods of predicting progression of disease.

In certain embodiments the methods involve estimation of 3D structures or measurement values of the equivalent 3D, from 2D projection radiographs. Subsequently, the methods involve generating an extrapolation of bone degradation or growth from one or more projection radiographs or 3D images (μCT, mri). This mathematical extrapolation is typically based on characterization of bone loss or growth trends of one or more sampling of images and other relevant patient information. For instance, a trend characterization can involve using measurements of microstructure and macro-anatomical parameters such as trabecular area ratio, trabecular thickness, cortical bone thickness and patient information such as age, gender, and ethnicity. The extrapolation calculation can be based on mathematical modeling of the physiology of bone remodeling using methods such as Monte-Carlo simulation, stochastic methods or artificial neural networks.

Using the techniques described herein, a correlation can be made between 3D trabecular volumetric measurements and 2D trabecular measurements. The relationship between these two measurements can be determined as a mathematical relationship that is non-linear, e.g. curvilinear, exponential, logarithmic, etc. Obtaining the mathematical relationship enables a more accurate simulation and enables thresholds to be calculated more accurately. Once the method to simulate bone loss is developed, it can be used to evaluate (measure) bone structure over time. From this a rate of erosion of bone loss can be modeled and, accordingly, a user can calibrate bone loss in the model that takes into consideration conditions present in actual population data. Once two data points are obtained for any patient, those data points can be compared to the population data to determine the likely rate of loss for that patient and to predict when a fracture would be likely to occur.

The first step is to locate a bone in the body of a subject, for example in a human body, for study. Once the bone is selected, an image or a series of images including the particular selected bone, e.g. hip, dental, spine, etc. are acquired. Images include, for example, conventional x-ray images, x-ray tomosynthesis, ultrasound (including A-scan, B-scan and C-scan) computed tomography (CT scan), magnetic resonance imaging (MRI), optical coherence tomography, single photon emission tomography (SPECT), and positron emission tomography, or such other imaging tools that a person of skill in the art would find useful in practicing the invention.

Once the image is taken, 3D structural representations can be generated from the data in the image, for example in a region of interest (ROI) located within the image. Algorithms can be used to automatically place regions of interest in a particular image. The quantitative and/or qualitative data extracted from the image and used to generate 3D structural prediction(s) includes, for example, the parameters and measurements shown in Table 1, Table 2 or Table 3.

Each step of locating a part of the body for study, optionally locating a region of interest, obtaining image data, and deriving data, can be repeated one or more times, respectively, as desired.

Image data can be optionally enhanced by applying image processing techniques, such as noise filtering or diffusion filtering, to facilitate further analysis.

TABLE 1 Representative Parameters Measured with Quantitative and Qualitative Image Analysis Methods PARAMETER MEASUREMENTS Bone density and Calibration phantom equivalent thickness microstructural (Average intensity value of the region of interest expressed as parameters thickness of calibration phantom that would produce the equivalent intensity) Trabecular contrast Standard deviation of background subtracted ROI Coefficient of Variation of ROI (Standard deviation/mean) (Trabecular equivalent thickness/Marrow equivalent thickness) Fractal dimension Hough transform Fourier spectral analysis (Mean transform coefficient absolute value and mean spatial first moment) Predominant orientation of spatial energy spectrum Trabecular area (Pixel count of extracted trabeculae) Trabecular area/Total area Trabecular perimeter (Count of trabecular pixels with marrow pixels in their neighborhood, proximity or vicinity) Trabecular distance transform (For each trabecular pixel, calculation of distance to closest marrow pixel) Marrow distance transform (For each marrow pixel, calculation of distance to closest trabecular pixel) Trabecular distance transform regional maximal values (mean, min., max, std. Dev). (Describes thickness and thickness variation of trabeculae) Marrow distance transform regional maximal values (mean, min., max, std. Dev) Star volume (Mean volume of all the parts of an object which can be seen unobscured from a random point inside the object in all possible directions) Trabecular Bone Pattern Factor (TBPf = (P1 − P2)/(A1 − A2) where P1 and A1 are the perimeter length and trabecular bone area before dilation and P2 and A2 corresponding values after a single pixel dilation, measure of connectivity) Connected skeleton count or Trees (T) Node count (N) Segment count (S) Node-to-node segment count (NN) Node-to-free-end segment count (NF) Node-to-node segment length (NNL) Node-to-free-end segment length (NFL) Free-end-to-free-end segment length (FFL) Node-to-node total struts length (NN.TSL) Free-end-to-free-ends total struts length(FF.TSL) Total struts length (TSL) FF.TSL/TSL NN.TSL/TSL Loop count (Lo) Loop area Mean distance transform values for each connected skeleton Mean distance transform values for each segment (Tb.Th) Mean distance transform values for each node-to-node segment (Tb.Th.NN) Mean distance transform values for each node-to-free-end segment (Tb.Th.NF) Orientation (angle) of each segment Angle between segments Length-thickness ratios (NNL/Tb.Th.NN) and (NFL/Tb.Th.NF) Interconnectivity index (ICI) ICI = (N * NN)/(T * (NF + 1)) Cartilage and Total cartilage volume cartilage Partial/Focal cartilage volume defect/diseased Cartilage thickness distribution (thickness map) cartilage parameters Mean cartilage thickness for total region or focal region Median cartilage thickness for total region or focal region Maximum cartilage thickness for total region or focal region Minimum cartilage thickness for total region or focal region 3D cartilage surface information for total region or focal region Cartilage curvature analysis for total region or focal region Volume of cartilage defect/diseased cartilage Depth of cartilage defect/diseased cartilage Area of cartilage defect/diseased cartilage 2D or 3D location of cartilage defect/diseased cartilage in articular surface 2D or 3D location of cartilage defect/diseased cartilage in relationship to weight-bearing area Ratio: diameter of cartilage defect or diseased cartilage/thickness of surrounding normal cartilage Ratio: depth of cartilage defect or diseased cartilage/thickness of surrounding normal cartilage Ratio: volume of cartilage defect or diseased cartilage/thickness of surrounding normal cartilage Ratio: surface area of cartilage defect or diseased cartilage/total joint or articular surface area Ratio: volume of cartilage defect or diseased cartilage/total cartilage volume Other articular Presence or absence of bone marrow edema parameters Volume of bone marrow edema Volume of bone marrow edema normalized by width, area, size, volume of femoral condyle(s)/tibial plateau/patella - other bones in other joints Presence or absence of osteophytes Presence or absence of subchondral cysts Presence or absence of subchondral sclerosis Volume of osteophytes Volume of subchondral cysts Volume of subchondral sclerosis Area of bone marrow edema Area of osteophytes Area of subchondral cysts Area of subchondral sclerosis Depth of bone marrow edema Depth of osteophytes Depth of subchondral cysts Depth of subchondral sclerosis Volume, area, depth of osteophytes, subchondral cysts, subchondral sclerosis normalized by width, area, size, volume of femoral condyle(s)/tibial plateau/patella - other bones in other joints Presence or absence of meniscal tear Presence or absence of cruciate ligament tear Presence or absence of collateral ligament tear Volume of menisci Ratio of volume of normal to torn/damaged or degenerated meniscal tissue Ratio of surface area of normal to torn/damaged or degenerated meniscal tissue Ratio of surface area of normal to torn/damaged or degenerated meniscal tissue to total joint or cartilage surface area Ratio of surface area of torn/damaged or degenerated meniscal tissue to total joint or cartilage surface area Size ratio of opposing articular surfaces Meniscal subluxation/dislocation in mm Index combining different articular parameters which can also include Presence or absence of cruciate or collateral ligament tear Body mass index, weight, height 3D surface contour information of subchondral bone Actual or predicted knee flexion angle during gait cycle (latter based on gait patterns from subjects with matching demographic data retrieved from motion profile database) Predicted knee rotation during gait cycle Predicted knee displacement during gait cycle Predicted load bearing line on cartilage surface during gait cycle and measurement of distance between load bearing line and cartilage defect/diseased cartilage Predicted load bearing area on cartilage surface during gait cycle and measurement of distance between load bearing area and cartilage defect/diseased cartilage Predicted load bearing line on cartilage surface during standing or different degrees of knee flexion and extension and measurement of distance between load bearing line and cartilage defect/diseased cartilage Predicted load bearing area on cartilage surface during standing or different degrees of knee flexion and extension and measurement of distance between load bearing area and cartilage defect/diseased cartilage Ratio of load bearing area to area of cartilage defect/diseased cartilage Percentage of load bearing area affected by cartilage disease Location of cartilage defect within load bearing area Load applied to cartilage defect, area of diseased cartilage Load applied to cartilage adjacent to cartilage defect, area of diseased cartilage

TABLE 2 Site specific measurement of bone parameters Parameters specific to All microarchitecture parameters on structures parallel to stress hip images lines All microarchitecture parameters on structures perpendicular to stress lines Geometry Shaft angle Neck angle Average and minimum diameter of femur neck Hip axis length CCD (caput-collum-diaphysis) angle Width of trochanteric region Largest cross-section of femur head Standard deviation of cortical bone thickness within ROI Minimum, maximum, mean and median thickness of cortical bone within ROI Hip joint space width Parameters specific to All microarchitecture parameters on vertical structures spine images All microarchitecture parameters on horizontal structures Geometry Superior endplate cortical thickness (anterior, center, posterior) Inferior endplate cortical thickness (anterior, center, posterior) Anterior vertebral wall cortical thickness (superior, center, inferior) Posterior vertebral wall cortical thickness (superior, center, inferior) Superior aspect of pedicle cortical thickness inferior aspect of pedicle cortical thickness Vertebral height (anterior, center, posterior) Vertebral diameter (superior, center, inferior), Pedicle thickness (supero-inferior direction). Maximum vertebral height Minimum vertebral height Average vertebral height Anterior vertebral height Medial vertebral height Posterior vertebral height Maximum inter-vertebral height Minimum inter-vertebral height Average inter-vertebral height Parameters specific to Average medial joint space width knee images Minimum medial joint space width Maximum medial joint space width Average lateral joint space width Minimum lateral joint space width Maximum lateral joint space width

TABLE 3 Measurements applicable on Microarchitecture and Macro-anatomical Structures Average density Calibrated density of ROI measurement Measurements on micro- The following parameters are derived from the extracted structures: anatomical structures of Calibrated density of extracted structures dental, spine, hip, knee or Calibrated density of background bone cores images Average intensity of extracted structures Average intensity of background (area other than extracted structures) Structural contrast (average intensity of extracted structures/ average intensity of background) Calibrated structural contrast (calibrated density extracted structures/calibrated density of background) Total area of extracted structures Total area of ROI Area of extracted structures normalized by total area of ROI Boundary lengths (perimeter) of extracted normalized by total area of ROI Number of structures normalized by area of ROI Trabecular bone pattern factor; measures concavity and convexity of structures Star volume of extracted structures Star volume of background Number of loops normalized by area of ROI Measurements on The following statistics are measured from the distance transform Distance transform of regional maximum values: extracted structures Average regional maximum thickness Standard deviation of regional maximum thickness Largest value of regional maximum thickness Median of regional maximum thickness Measurements on Average length of networks (units of connected segments) skeleton of extracted Maximum length of networks structures Average thickness of structure units (average distance transform values along skeleton) Maximum thickness of structure units (maximum distance transform values along skeleton) Number of nodes normalized by ROI area Number of segments normalized by ROI area Number of free-end segments normalized by ROI area Number of inner (node-to-node) segments normalized ROI area Average segment lengths Average free-end segment lengths Average inner segment lengths Average orientation angle of segments Average orientation angle of inner segments Segment tortuosity; a measure of straightness Segment solidity; another measure of straightness Average thickness of segments (average distance transform values along skeleton segments) Average thickness of free-end segments Average thickness of inner segments Ratio of inner segment lengths to inner segment thickness Ratio of free-end segment lengths to free-end segment thickness Interconnectivity index; a function of number of inner segments, free-end segments and number of networks. Directional skeleton All measurement of skeleton segments can be constrained by segment one or more desired orientation by measuring only skeleton measurements segments within ranges of angle. Watershed Watershed segmentation is applied to gray level images. segmentation Statistics of watershed segments are: Total area of segments Number of segments normalized by total area of segments Average area of segments Standard deviation of segment area Smallest segment area Largest segment area

As will be appreciated by those of skill in the art, the parameters and measurements shown in Tables 1, 2 and 3 are provided for illustration purposes and are not intended to be limiting. It will be apparent that the terms micro-structural parameters, micro-architecture, micro-anatomic structure, micro-structural and trabecular architecture may be used interchangeably. In addition, other parameters and measurements, ratios, derived values or indices can be used to extract quantitative and/or qualitative information without departing from the scope of the invention. See, e.g., co-owned International Application WO 02/30283.

Extracted structures typically refer to simplified or amplified representations of features derived from images. An example would be binary images of trabecular patterns generated by background subtraction and thresholding. Another example would be binary images of cortical bone generated by applying an edge filter and thresholding. The binary images can be superimposed on gray level images to generate gray level patterns of structure of interest.

FIG. 1 shows an extrapolation of bone loss as generated from a 2D image of spine. Serial erosions are conducted on the image. An estimate of the most likely (e.g. maximum likelihood (non-Bayesian, classical approach) or maximum a-posteriori (Bayesian approach)) model for the volumetric structure that resulted in the 2-D projection structure shown in FIG. 1 can be achieved and is shown in FIG. 3.

Once the most likely 3-D structure model is obtained (e.g. FIG. 3) the corresponding 3-D parameters, which are easier to understand and more intuitive to analyze, can be used. In the event that it is determined that these parameters do not correlate well, additional parameters can be included. Thus a combination of 2D and 3D parameters can be used. Additionally, a family of models can be obtained from, for example, the 2-D structure of FIG. 1.

Specifically, staging or progression can be estimated by associating growth models to the nodes, rods and plates according to what is known about how a specific treatment affects these specific structures. For example, if a specific treatment is supposed to increase mineral deposition on the volume, the mineral diffusion from the blood rich regions towards the rest of the volume can be used to predict increase or decrease of density at several different stages.

The flowchart shown in FIG. 11 depicts exemplary steps and information that can be used to predict fracture risk and/or generate a fracture risk index. A 2D digital image (e.g., digitized radiographs, digital detector radiograph, etc.) including bone is taken using standard techniques and a 3D structure prediction engine generates the most probable 3D structure given the 2D image. Optionally, a-priori knowledge of the most probable 3D structure in various regions of bones stored in an anatomic structure database, may be used to predict the 3D structure using techniques such as (including but not limited to) Bayesian inference methods, Monte Carlo simulations, artificial neural networks, etc. The anatomic structure database may contain probabilistic or functional models, numerical characteristics and 2D and/or 3D images of bone structures of various regions of bones.

Simulated remodeling is then applied to the predicted 3D structure, optionally using one or more remodeling characteristics of therapeutic interventions and/or or disease progression. The simulated bone remodeling engine generates the outcome of bone structure due to therapeutic interventions and/or disease progression at one or more time intervals. The remodeling characteristics can include data such as bone resorption and formation rates, measurements of hormonal levels, age, etc. Techniques such as morphological operations in combination with stochastic methods, Monte-Carlo simulations, artificial neural networks, etc, and be use to simulate bone remodeling. Optionally, a database containing a collection of bone remodeling characteristics of various therapeutics intervention modalities (chemical, physical, electromagnetic radiation, etc), and various stages of disease progression can be maintained to be used as reference sources for therapeutic specific or disease condition specific remodeling simulations.

Following remodeling of the predicted 3D structure, structure strength may be predicted using computational biomechanics modeling methods such as finite element analysis, curved bean model simulations, etc. on the 3D structures and/or on reprojected 2D structures. Optionally, the 2D and/or 3D structures can be analyzed to obtain the parameters described in Tables 1, 2 ,and 3. These parameters are subsequently used to predict structural strength by referencing to one or more structural strength databases. The databases may contain information that relate the measured structure parameters to structural strength.

Finally, fracture risk can be predicted as a fracture risk index generated in terms of the predicted structural strength, and optionally, in combination with other risk factors.

In various embodiments of the invention, one or more measurements pertaining to, without limitation, bone mineral density, bone architecture or structure, macro-anatomy, and/or bone biomechanics, may be generated from two or more x-ray beam rotation angles. The x-rays may be generated, without limitation, by a conventional radiography unit, a conventional tomography unit (CT scan), or a digital radiography unit (e.g., digital radiography (DR) or computed radiography (CR) systems) (see, for example, The Essential Physics of Medical Imaging, editors Bushberg, Seibert, Leidholdt Jr & Boone, 2002, Lippincott, Williams & Wilkins, incorporated herein by reference in its entirety). If a DR or CR system is implemented, images may be obtained from multiple rotation angles so as to allow tomographic reconstruction.

The use of multiple x-ray beam rotation angles advantageously may be used to identify anatomical landmarks more reliably. Reproducibility may be improved. Furthermore, the use of multiple x-ray beam rotation angles may be used for semi or true three-dimensional and/or volume assessments.

A combination of the above-described parameters (i.e., bone mineral density, bone architecture or structure, macro-anatomy, and bone biomechanics) may be assessed in two-dimensions and/or three-dimensions to determine, without limitation, a patient's bone fracture risk.

While the invention has been described in conjunction with the preferred specific embodiments thereof, it is to be understood that the foregoing description as well as the examples which follow are intended to illustrate and not limit the scope of the invention. Other aspects, advantages and modifications within the scope of the invention will be apparent to those skilled in the art to which the invention pertains.

EXAMPLES Example 1 FEA Analysis of Bone Strength Based of Projection of Bone Remodeling for Prediction of Fracture Risk

A fracture risk index is created for a specific patient following the steps outlined in FIG. 11 and shown to the patient to illustrate the condition of their bone(s) at a projected time in the future, for example 2 years, thereby demonstrating the bone loss that may occur without intervention (e.g., treatment).

In one example, the projected model can be used to advise a patient, for example, that after taking a particular treatment course of action the bone would be projected to look like A, whereas failing to treat the bone, the bone would degenerate to B. Thus providing an aid to illustrate and explain to patients different treatment options and how they would reflect in terms of the risk of having a fracture. For example, the model could be used to show that a treatment course could reduce fracture risk by 50% whereas non-treatment increases the fracture risk by, for example, 80%. 

What is claimed is:
 1. A method for analyzing bone structure or bone density, the method comprising the steps of: obtaining an image of a subject, wherein the image comprises an image of the subject's bone; estimating probable volumetric structure of bone; and measuring one or more parameters of estimated volumetric structure of bone.
 2. A method for monitoring the ability of an agent to affect bone quality, the method comprising the steps of (a) obtaining bone quality measurements on a subject, wherein the bone quality measurements are obtained using the method according to claim 1; (b) administering an agent to the subject; (c) obtaining bone quality measurements of the subject after administration of the agent, wherein the bone quality measurements are obtained using the method according to claim 1; (d) comparing bone quality measurements from steps (a) and (c), wherein a difference between in bone quality measurements between (a) and (c) is due to the effect of the agent. 